Vaginal hydrogel for delivery of therapeutics

ABSTRACT

The composition is a hydrogel which may be used to deliver therapeutics vaginally. The hydrogel may include a glycosaminoglycan. The glycosaminoglycan may include multiple thiol groups. The composition may also include a molecule that includes at least two thiol reactive sites. The composition may include a mucoadhesive agent as well as a therapeutic agent. The composition may deliver the therapeutic at a pH that is optimal for the vaginal environment, namely between about 3.5 and 5.0.

RELATED APPLICATIONS

This application is a continuation application of U.S. patentapplication Ser. No. 16/233,102, filed Dec. 27, 2018, which claims thebenefit of U.S. Provisional Patent Application No. 62/645,801, filedMar. 21, 2018, each of which is hereby incorporated by reference in itsentirety.

TECHNICAL FIELD

This disclosure relates to compounds and methods of drug delivery, inparticular, delivery of gynecological therapeutic compounds.

BACKGROUND

Bacterial Vaginosis:

Vaginitis affects millions of women around the world every year, andbacterial vaginosis is the most common form. Currently, marketedtreatments are either intravaginal creams and gels or systemic oraltreatments, and the most common drugs are metronidazole, clindamycin,and tinidazole. Metronidazole is the most common drug due to the highefficacy of treating harmful bacteria, along with the lack of effect onbeneficial lactobacilli. Some of the problems, however, with currenttreatments include the messiness of intravaginal gels and creams, thepotentially lowered efficacy of the drugs in gels and creams as the drugis lost through vaginal secretions, pH imbalances with products that donot have pHs of 3.5-5, and for systemic treatments, the problem ofintroducing the drugs to the entire body, which can produce sideeffects. Therefore, a better method for effectively deliveringmetronidazole or other therapeutics to the vagina over multiple days, ata proper pH for the vaginal environment, and with high drug efficacy isneeded.

Hydrogels and Films:

Hydrogels have been utilized as a biomaterial in a variety of medicalapplications owing to their high water content, similarity in physicalproperties to many tissues, and potential for incorporating drugs. Theseapplications include wound healing, tissue engineering and regenerativemedicine, drug delivery, and joint lubrication. These hydrogels can bebased on natural or synthetic materials, or a combination of the two.Typically, hydrogels will be crosslinked, either through physicalinteraction—such as simple entanglement, hydrogen bonding, or ionicinteraction—or through covalent bonds. Either method of forminghydrogels is typically done at or near what is considered standardphysiological pH (i.e., pH 7.4). However, many environments in the bodyare at a lower pH. In particular, the average pH of the vagina istypically between about 3.2 and 5.0, an environment that favorsmicroflora that are beneficial to the vagina. If the pH of the vagina isincreased, a shift in the balance of the microflora occurs, allowing forinfection and eventually leading to vaginosis or vaginitis.

Currently available treatments often treat either the infection or theinflammation, but not both. Additionally, many of these treatments areprovided in either a liquid or hydrogel format, but not at a pH that isbeneficial for the vaginal environment. As indicated above, a filmformat may be easier to use and provide better drug delivery andefficacy.

Thus, there is a need for a film formed from a hydrogel that can bedelivered vaginally and that is at a pH targeted for this environment,namely between about 3.5 and 5.0, and which may be used for delivery oftherapeutics.

BRIEF SUMMARY OF THE DISCLOSURE

We disclose a composition which may be used to deliver a therapeuticagent vaginally. The composition may include one or moreglycosaminoglycans. Each of the one or more glycosaminoglycans mayinclude a plurality of thiol groups. The composition may also include amolecule that includes at least two thiol-reactive sites. In an example,the molecule may be poly(ethylene glycol) diacrylate or poly(ethyleneglycol) bisbromoacetate. The thiol-reactive sites may be chosen from alist that includes, but is not limited to, acrylate, methacrylate,bromoacetate, iodoacetate, bromoacetamide, iodoacetamide, or maleimide.The composition may also include a mucoadhesive agent. In an example,the mucoadhesive agent may be methylcellulose, hydroxymethylcellulose,hydroxyethylcellulose, or hydroxypropylcellulose. The composition may beprovided in a dried form and have a pH of between about 3.2 and about5.0 when hydrated. A therapeutic agent may be included in thecomposition.

In some embodiments, the one or more glycosaminoglycan comprises amodified hyaluronic acid. In an example, the modified hyaluronic acid isa thiol-modified hyaluronic acid. In an example, the thiol-modifiedhyaluronic acid may be crosslinked to a poly(ethylene glycol) whichincludes a plurality of thiol-reactive sites.

In some embodiments, the therapeutic agent which may be included in thecomposition may include one or more of the agents in the following list:an antimicrobial agent, an antibacterial agent, an antiviral agent, anestrogen, and an estrogen derivative.

In some embodiments, the therapeutic agent may have a solubility inwater of less than about 1.0 mg/ml. In some embodiments, the therapeuticagent may have a concentration in the composition which is at leastabout 10 times greater than the solubility of the therapeutic agent inwater. In some embodiments, the concentration of the therapeutic agentis at least about 100 times greater than the solubility of thetherapeutic agent in water.

We also disclose a method for making a drug delivery compositionincluding the step of forming a mixture of glycosaminoglycan that hasmultiple thiol groups, a molecule that includes at least twothiol-reactive sites, a mucoadhesive agent, a therapeutic agent, and abuffer which has a pH between about 3.2 and about 5.0. Theglycosaminoglycan and the molecule may be allowed to covalentlycrosslink; and the mixture allowed to dry.

BRIEF DESCRIPTION OF THE DRAWINGS

In order that the advantages of the invention will be readilyunderstood, a more particular description of the invention brieflydescribed above will be rendered by reference to specific embodimentsillustrated in the appended drawings. Understanding that these drawingsdepict only typical embodiments of the invention and are not thereforeto be considered limiting of its scope, the invention will be describedand explained with additional specificity and detail through use of theaccompanying drawings.

FIG. 1 is a graph which illustrates the cumulative drug release over 144hours from the films containing 10 mg/ml metronidazole (M) ormetronidazole benzoate (MB).

FIG. 2 is a graph which illustrates the cumulative drug release over 144hours from the films containing 20 mg/ml metronidazole (M) ormetronidazole benzoate (MB).

FIG. 3 is a bar graph which illustrates the swelling of metronidazoleand metronidazole benzoate films after rehydrating in simulated vaginalfluid (SVF) for 24 hours.

FIG. 4 is a graph which illustrates stress vs strain curve for filmscontaining 5 mg/ml methylcellulose during tensile testing.

FIG. 5 is a graph which illustrates stress vs strain curves for filmscontaining 7.5 mg/ml methylcellulose during tensile testing.

DETAILED DESCRIPTION OF THE DISCLOSURE Definitions

The following terms and phrases have the meanings indicated below,unless otherwise provided herein. This disclosure may employ other termsand phrases not expressly defined herein. Such other terms and phrasesshall have the meanings that they would possess within the context ofthis disclosure to those of ordinary skill in the art. In someinstances, a term or phrase may be defined in the singular or plural. Insuch instances, it is understood that any term in the singular mayinclude its plural counterpart and vice versa, unless expresslyindicated to the contrary.

As used herein, the singular forms “a,” “an,” and “the” include pluralreferents unless the context clearly dictates otherwise. For example,reference to “a substituent” encompasses a single substituent as well astwo or more substituents, and the like.

As used herein, “for example,” “for instance,” “such as,” or “including”are meant to introduce examples that further clarify more generalsubject matter. Unless otherwise expressly indicated, such examples areprovided only as an aid for understanding embodiments illustrated in thepresent disclosure, and are not meant to be limiting in any fashion. Nordo these phrases indicate any kind of preference for the disclosedembodiment.

While this invention is susceptible of embodiment in many differentforms, there are shown in the drawings, which will herein be describedin detail, several specific embodiments with the understanding that thepresent disclosure is to be considered as an exemplification of theprincipals of the invention and is not intended to limit the inventionto the illustrated embodiments.

Covalent crosslinking of the hydrogels described herein, and the filmsformed from them, may be achieved through means including, but notlimited to, disulfide crosslinking, Michael-type addition, orphotopolymerization. The hydrogel may be based on an anionicpolysaccharide, which may be naturally anionic (for example, hyaluronicacid or alginate), or may be modified to introduce or increase negativecharge, for example, through substitution of hydroxyl groups withcarboxyl groups. Particularly suitable are glycosaminoglycans, and amodified hyaluronic acid (HA). HA is a natural anionic polysaccharidethat is found throughout the body and has been shown to haveanti-inflammatory properties. Additionally, HA provides moisturizationand lubrication.

The hyaluronic acid may be modified to have a higher number of negativecharges (e.g., carboxymethyl hyaluronic acid) for ionic crosslinking,and/or to include groups capable of covalent crosslinking, for example,thiol or amine groups, thiol-reactive or amine-reactive groups, orphotopolymerizable groups. These photopolymerizable groups may includemethacrylate, acrylate, or vinyl groups. The chemical structure ofhyaluronic acid, along with modifications mentioned above, is shownbelow. The R groups indicated are modifications made to introduce groupsfor altering material properties or for crosslinking. In the case of athiol-modified HA, the hydrogel may be formed by disulfide crosslinkingor by combining with a molecule having thiol-reactive groups.

One common crosslinker is poly(ethylene glycol) (PEG), which can bemodified to have reactive endgroups, for example, bromoacetate oracrylate groups, added to aid in crosslinking. The chemical structure ofpoly(ethylene glycol) is shown below. The R groups indicated aremodifications made to introduce reactive endgroups for crosslinking.Although the addition of both bromoacetate or acrylate groups areexamples of Michael-type addition, the crosslinking reaction of a thiolwith bromoacetate occurs faster than a thiol with acrylate. Otherthiol-reactive endgroups could also be used to crosslink a thiolatedpolysaccharide. Alternatively, PEG with photopolymerizable endgroupscould be used in conjunction with a hyaluronic acid or otherpolysaccharide having photopolymerizable endgroups, allowing foraltering of material properties for the resultant photocrosslinkedhydrogel.

Thiol groups on the anionic polysaccharide are useful, as thiol groupsmay be beneficial for interacting with the vaginal mucosa, allowing thehydrogel film to remain in the vagina for an extended period of time.For example, when the hydrogel composition has a thiolatedpolysaccharide and is combined with a thiol-reactive molecule, the ratioof thiol groups to thiol-reactive groups may be about 2:1 or greater.This can allow for some thiols to be used for covalent crosslinking,while having thiol groups remaining that may be used to interact withthe vaginal mucosa.

The hydrogels may be formed at a pH between about 3.5 and 5.0, utilizingan appropriate buffer, for example, a lactic acid or citric acid buffer.A lactic acid buffer may be particularly appropriate for the vaginalenvironment, as lactic acid/lactate is produced naturally in the vagina.Crosslinking via Michael-type addition is typically done at a pH ofabout 6.5-8.5, as the crosslinking proceeds extremely slowly outside ofthis range. However, to ensure proper hydrogel formation at lower pH,such as between 3.5 and 5.0, the crosslinking mixture may be placed in asealed, humidified environment for several days until the hydrogel hasformed. Additionally, the temperature of the humidified environment maybe increased slightly during this time (to ˜35-40° C.) to facilitatecrosslinking without degrading the polysaccharide.

The crosslinking solution may be placed in a mold in which the hydrogelwill take the shape of the mold, but the hydrogel and/or resultant filmdoes not adhere to the mold and is therefore easily released. Once thehydrogel has formed, a film may be formed from the hydrogel by eitherallowing the hydrogel to air dry, or by freezing and lyophilizing thehydrogel. Air drying will result in a film that is much thinner than theoriginal hydrogel, whereas lyophilization will result in a film with aspongier texture that has a shape very similar to the original hydrogel.The dried film or sponge may then be ground into a powder, if desired.

The resultant hydrogel may be more or less tightly crosslinked byvarying the degree of covalent crosslinking in the hydrogel. This may beaccomplished by changing the concentration of the polysaccharide, anadditional crosslinking molecule, or the number of reactive groups onthe polysaccharide or additional crosslinking molecule.

One or more therapeutic agents may be incorporated within the gel, andmay be incorporated by mixing, covalently attaching the therapeuticagent to a component of the gel, or through ionic interaction with acomponent of the gel. The one or more therapeutic agents may includeantimicrobials, for example, antibiotics and antivirals, hormones, forexample, estrogen or an estrogen derivative, steroids, andanti-inflammatories. A therapeutic agent with a lower solubility inwater will release more slowly from the gel, leading to extendeddelivery of the therapeutic. The therapeutic agent can be incorporatedwithin the gel at concentrations higher than the solubility of thetherapeutic agent in water, although the insoluble amount will appear assmall particles within the hydrogel and resultant dried material. In anexample, the therapeutic agent may have a solubility in water of lessthan about 1.0 mg/ml. In an example, the therapeutic agent may have aconcentration in the composition at least about 10 times greater thanthe solubility of the therapeutic agent in water. In an example, thetherapeutic agent may have a concentration in the composition at leastabout 100 times greater than the solubility of the therapeutic agent inwater.

Other components may also be incorporated into the hydrogel to aid inflexibility of the resultant films, enhance mucoadhesion to tissue, orboth. Mucoadhesive agents include cellulose derivatives, for example,methylcellulose, hydroxymethylcellulose, hydroxyethylcellulose, andhydroxypropylcellulose. The cellulose derivatives may also improveflexibility of the hydrogel films.

EXAMPLES

Materials

Thiol-Crosslinked Films:

Thiolated carboxymethyl HA (CMHA-S; 10 mg/mL), poly(ethyleneglycol)-diacrylate (PEGda, MW=3350; 5.86 mg/mL), poly(ethyleneglycol)-bisbromoacetate (PEGbba, MW=3350; 5.86 mg/mL), methylcellulose(MC; 5 or 7.5 mg/mL).

Drugs:

metronidazole (5-37.5 mg/mL), metronidazole benzoate (5-37.5 mg/mL).

Lactic Acid Buffer:

30.36 mM sodium lactate, 22 mM lactic acid, 8 mg/mL sodium chloride, inDI H₂O, pH 4-5.

Simulated Vaginal Fluid (SVF):

sodium chloride (3.51 g/L), calcium hydroxide (222 mg/L), urea (400mg/L), glucose (5.00 g/L), bovine serum albumin (18 mg/L), potassiumhydroxide (24.96 μl/L), glycerol (126.88 μl/L), acetic acid (0.954ml/L), lactic acid (1.958 ml/L).

Phosphate Buffered Saline (PBS):

sodium chloride (8 g/L), potassium chloride (0.2 g/L), sodium phosphate(1.44 g/L), potassium phosphate (0.24 g/L), in DI H₂O, pH 7.4.

Photo-Crosslinked Films:

methacrylated HA (HAMA; 10 mg/mL), PEGda (25 mg/mL),2,2-dimethoxy-2-phenyl acetophenone (DMPA) or Irgacure 2959 (10 μl/mL),methylcellulose (5 mg/mL).

Molds Used to Create Hydrogels:

polyvinyl chloride (PVC), polycarbonate base with silicone sides,silicone.

Example 1—Creating Thiol-Crosslinked Films

CMHA-S was dissolved in lactic acid buffer; methylcellulose and drugwere then added to the CMHA-S solution. PEGbba was separately dissolvedin lactic acid buffer. The CMHA-S solution and PEGbba solution were thencombined and mixed by inversion or drawing up and down a pipette. Thefinal mixture had concentrations of CMHA-S, PEGbba, MC, and drug asindicated above under “Materials”. The final mixture was thentransferred to a mold. The mold was placed in a container along withopen dishes of water to provide humidity, and a lid placed on thecontainer to seal the container, preventing water from evaporating fromthe mixture during crosslinking and formation of the hydrogel. A smallportion of the final mixture was also placed in a sealed tube to monitorcrosslinking. When crosslinking was complete, the lid was removed fromthe container and the hydrogel was allowed to air dry, forming a thinfilm.

For this combination of CMHA-S and PEGbba in lactic acid buffer having apH of 4.5, the mixture crosslinked and formed a solid hydrogel inapproximately 72 hours. Insoluble drug that had been incorporated withinthe mixture could be seen as small particles dispersed within thehydrogel and in the resultant thin film.

Example 2—Drug Release from Thiol-Crosslinked Films

Five 6 mm-diameter discs were punched out from each film formulationlisted in Table 1. Each disc was placed in 1 ml of SVF in amicrocentrifuge tube; the tubes were then placed in an incubator shakerat 37° C. The SVF release medium was removed and replaced with fresh SVFat 0.5, 1, 2, 4, 8, 24, 48, 96, and 144 hours. Aliquots of the SVFrelease medium from each sample at each time point were placed in aplate reader and the absorbance at 318 nm was determined. A standardcurve of the drug (metronidazole or metronidazole benzoate) in SVF wasused to calculate the concentration of drug in each sample of SVFrelease medium.

TABLE 1 Formulations of thiol-crosslinked films used in testing. Allformulations had 10 mg/ml CMHA-S and 5.86 mg/ml PEGbba. Films werecreated according to the method in Example 1, utilizing silicone molds.Drug Methylcellulose Form- concentration concentration ulation # Drug(mg/ml) (mg/ml) 1 Metronidazole benzoate 10 5 2 Metronidazole benzoate20 5 3 Metronidazole benzoate 10 7.5 4 Metronidazole benzoate 20 7.5 5Metronidazole 10 5 6 Metronidazole 20 5 7 Metronidazole 10 7.5 8Metronidazole 20 7.5

Release of metronidazole and metronidazole benzoate fromthiol-crosslinked films is shown in FIGS. 1 and 2 . More specifically,FIG. 1 is a graph which illustrates the cumulative drug release over 144hours from the films containing 10 mg/mL metronidazole (M) ormetronidazole benzoate (MB) while FIG. 2 is a graph which illustratesthe cumulative drug release over 144 hours from the films containing 20mg/mL metronidazole (M) or metronidazole benzoate (MB). While themetronidazole benzoate films released drug steadily over time, themetronidazole films dumped most of the released drug within an hour,which is likely due to the solubility differences between the drugs(solubility in water: 10 mg/ml vs 0.1 mg/ml for metronidazole andmetronidazole benzoate, respectively). The metronidazole benzoate filmsalso released more total drug than did the metronidazole films. Theconcentration of MC also seemed to have an effect on the release of thedrug, particularly for the metronidazole benzoate films. The films withthe higher MC concentration released more drug over time than the filmswith lower MC concentration; thus, MC may aid in drug release. Both ofthe metronidazole benzoate films with high MC concentration were alsothe ones to release the highest percentage of drug, relative to thepredicted amount in each disc.

Example 3—Material Properties of Thiol-Crosslinked Films

Film Flexibility:

A qualitative assessment of film flexibility was performed by twisting,folding, and crumpling of the films. The metronidazole films were verybrittle and had very little give. They could not be stretched at all,which was one characteristic property of the films without drug; norcould they be twisted. They would immediately break upon any twisting,and the films could not even reach a 90° twist. Additionally, they couldbe loosely folded, but not creased without breaking, and could thereforenot be crumpled. The metronidazole benzoate films, on the other hand,could be folded, creased, and crumpled without any damage to the films.They could also be twisted at least 180° before any tearing occurred.The difference in flexibility between the metronidazole andmetronidazole benzoate films is likely due to the higher concentrationof actual dissolved drug in the metronidazole films, which more directlyaffects the film properties. The high MC concentration also aided inflexibility, though less so for the metronidazole films.

Mucoadhesivity:

The mucoadhesivity of films containing metronidazole benzoate and filmswithout drug was assessed using bovine vaginal tissue. A piece ofvaginal tissue was affixed to a half-cylinder of PVC pipe usingsuperglue, such that the mucosal lining was facing outward. The PVC pipewas propped at an approximate 60° angle to simulate use under gravity. Astrip of the film was placed on the mucosal lining. A syringe filledwith SVF was placed in a syringe pump, and tubing was attached to thesyringe with the outlet of the tubing placed just above the film on thetissue. The syringe pump was run at 2 different rates—1 ml/min, tosimulate a rush of vaginal fluid, for 3 minutes; and 1.4 μl/min, tosimulate average normal vaginal secretion, for up to 24 hours. The filmwas monitored for any slippage of the film during fluid flow. The filmsswelled as they became rehydrated with SVF, and some buckling of thefilms was noted during rehydration. However, all films remained incontact with the tissue throughout the testing and did not have anyslippage. Therefore, the films demonstrated mucoadhesive properties, andswelling of the films during rehydration did not interfere with thefilms' interaction with the tissue.

Swelling:

To further assess swelling of the films when rehydrated, three 6mm-diameter discs were punched out from each film formulation shown inTable 1. The discs were placed in a 24-well plate with 1 ml of SVF ineach well. The film discs were allowed to rehydrate and swell in the SVFfor 24 hours at 37° C. Images of the rehydrated discs were then takenusing a stereomicroscope with camera attached, and diameters of thediscs were determined using Image-J software. All of the filmformulations swelled to about 8 mm in diameter as shown in FIG. 3 .Although there was some slight variability with the differentformulations, there was no significant difference in swelling whencomparing the different film formulations. This swelling outward of thefilm is probably a rather beneficial property, as it provides moresurface area for the film to interact with the mucosal lining.

Tensile Properties:

A dog-bone-shaped mold was used to cut five pieces of film from eachmetronidazole benzoate formulation and three pieces for each no drugformulation. The gage area of the cutouts measured 8 mm in length, 3 mmin width, and were approximately 0.1 mm and 0.25 mm in thickness for thefilms without and with drug, respectively. Each end of the film pieceswas placed between the clamps of an Instron 5943. Tensile testing of thefilm pieces was performed, using a crosshead speed of 0.25 mm/min. Eachtrial was concluded when the film was fully torn across the gage area.

The results of the tensile strength tests were often highly variable asshown in FIGS. 4 and 5 . Specifically, FIG. 4 illustrates the stress vsstrain curve for films containing 5 mg/ml methylcellulose during tensiletesting and FIG. 5 illustrates the stress vs strain curve for filmscontaining 7.5 mg/ml methylcellulose during tensile testing. Thisvariability may be due to the fact that the solutions used for the filmsare not homogeneous. In particular, the dispersal of the poorly solubledrug, and even the crosslinks between chains, are random and uneven.Therefore, each piece of film may behave differently from another pieceof film, even from the same solution, and any visibly undetectablebreaks along the edge of the gage area may create a false fail location.Therefore, hundreds of trials with each formulation may be necessary toacquire statistically significant data. Alternatively, a method ofrendering the films more homogeneous may be useful.

Two of the measures that may be important for assessing film propertiesfrom this testing are the ultimate tensile strength (maximum stressachieved for the material during testing) and the strain at breakage.Regardless of the concentration of methylcellulose, an increased amountof drug in the film resulted in a significant decrease in the ultimatetensile strength. Further, the concentration of methylcellulose did nothave a significant effect on the ultimate tensile strength, as thestrength was similar when comparing formulations with the same amount ofdrug but different concentrations of methylcellulose. The strain atbreakage, on the other hand, did not appear to be dependent on drug ormethylcellulose concentration.

Example 4—Creating Photo-Crosslinked Films

HAMA was dissolved in lactic acid buffer; methylcellulose and drug werethen added to the HAMA solution. PEGda was separately dissolved inlactic acid buffer. The HAMA solution and PEGda solution were thencombined and mixed by inversion or drawing up and down a pipette.Photoinitiator, either DMPA or Irgacure, was then added and mixed byinversion. The final mixture had concentrations of HAMA, PEGda, MC,drug, and photoinitiator as indicated above under “Materials”. The finalmixture was then transferred to a mold. The mold was placed under a 365nm-wavelength UV lamp for up to 10 minutes until the mixture wascrosslinked, forming a hydrogel. The hydrogel was then allowed to airdry, forming a thin film.

Modifications and improvements of the embodiments specifically disclosedherein are within the scope of the following claims. Without furtherelaboration, it is believed that one skilled in the area can, using thepreceding description, utilize the present disclosure to its fullestextent. Therefore, the Examples herein are to be construed as merelyillustrative and not a limitation of the scope of the present inventionin any way. The embodiments disclosed in which an exclusive property orprivilege is claimed are defined as follows.

We claim:
 1. A crosslinked composition comprising: a glycosaminoglycancomprising a plurality of thiol-reactive sites, a molecule A comprisingat least two thiol groups, a mucoadhesive agent, and a therapeutic agenthaving a solubility in water of less than about 1.0 mg/mL, wherein thecomposition is dried by a process selected from air drying orlyophilization, and wherein the glycosaminoglycan is crosslinked to themolecule A at a pH selected from a value between about 3.2 and about5.0.
 2. The crosslinked composition of claim 1, wherein theglycosaminoglycan comprises a modified hyaluronic acid.
 3. Thecrosslinked composition of claim 1, wherein the glycosaminoglycancomprises methacrylated or acrylated hyaluronic acid.
 4. The crosslinkedcomposition of claim 1, wherein the molecule A comprises a thiolatedpoly(ethylene glycol).
 5. The crosslinked composition of claim 1,wherein the therapeutic agent has a concentration in the composition atleast about 10 times greater than the solubility in water.
 6. Thecrosslinked composition of claim 4, wherein the therapeutic agent has aconcentration in the composition at least about 100 times greater thanthe solubility in water.
 7. The crosslinked composition of claim 1,wherein the at least two thiol-reactive sites are independently selectedfrom the group consisting of acrylate, methacrylate, bromoacetate,iodoacetate, bromoacetamide, iodoacetamide, and maleimide.
 8. Thecrosslinked composition of claim 1, wherein the mucoadhesive agent isselected from the group consisting of methylcellulose,hydroxymethylcellulose, hydroxyethylcellulose, andhydroxypropylcellulose.
 9. The crosslinked composition of claim 1,wherein the therapeutic agent comprises one or more of distinct agentsin the following list: an antimicrobial agent, an antibacterial agent,an antiviral agent, an estrogen, and an estrogen derivative.
 10. Thecrosslinked composition of claim 1, wherein the glycosaminoglycan iscrosslinked to the molecule A at a pH consisting of a value betweenabout 3.5 and about 4.5.
 11. A method for making a crosslinked drugdelivery composition comprising: forming a mixture comprising: aglycosaminoglycan comprising a plurality of thiol-reactive sites, amolecule A comprising at least two thiol groups, a mucoadhesive agent, atherapeutic agent having a solubility in water of less than about 1.0mg/mL, and a buffer having a pH between about 3.2 and about 5.0;crosslinking the glycosaminoglycan and the molecule A at a pH selectedfrom a value between about 3.2 and about 5.0; and drying the crosslinkedmixture by a process selected from air drying or lyophilization.
 12. Themethod of claim 11, wherein the glycosaminoglycan comprises a modifiedhyaluronic acid.
 13. The method of claim 11, wherein theglycosaminoglycan comprises methacrylated or acrylated hyaluronic acid.14. The method of claim 11, wherein the molecule A comprises a thiolatedpoly(ethylene glycol).
 15. The method of claim 11, wherein thetherapeutic agent is provided in the composition in a concentration ofat least about 10 times greater than the solubility in water.
 16. Acrosslinked drug delivery composition made by the method of claim 11.17. A crosslinked composition comprising: a modified hyaluronic acidcomprising a plurality of thiol-reactive sites, poly(ethylene glycol)comprising at least two thiol groups, and a therapeutic agent, whereinthe modified hyaluronic acid is crosslinked to the poly(ethylene glycol)at a pH selected from a value between about 3.2 and about 5.0, and thecomposition is dried by a process selected from air drying orlyophilization.
 18. The crosslinked composition of claim 17, wherein thethiol-reactive sites are independently selected from the groupconsisting of acrylate, methacrylate, bromoacetate, iodoacetate,bromoacetamide, iodoacetamide, and maleimide.
 19. The crosslinkedcomposition of claim 17, wherein the therapeutic agent comprises one ormore of distinct agents in the following list: an antimicrobial agent,an antibacterial agent, an antiviral agent, an estrogen, and an estrogenderivative.
 20. The crosslinked composition of claim 17, wherein thetherapeutic agent is provided in the composition in a concentration ofat least about 10 times greater than the solubility in water.